Ultrasound diagnostic apparatus and operation method of ultrasound diagnostic apparatus

ABSTRACT

An ultrasound transducer unit including a plurality of ultrasound transducers transmits and receives ultrasound waves to and from an inside of a subject. In a case where a checking operation unit is operated, a controller controls a driving voltage supply unit such that a driving voltage is supplied with all of the plurality of ultrasound transducers as driving target transducers. In a case where the checking operation unit is operated, a depolarization determination unit calculates, for each ultrasound transducer, a reception sensitivity in a case where an ultrasound wave is received by driving all of the plurality of ultrasound transducers as the driving target transducers, and determines whether or not a depolarization determination value calculated from the reception sensitivity of each ultrasound transducer satisfies numerical conditions. If the numerical conditions are satisfied, a polarization voltage supply unit supplies a polarization voltage to each of the plurality of ultrasound transducers.

CROSS-REFERENCE TO RELATED APPLICATIONS

This application is a divisional application of copending U.S.Application No. 16/419,595, filed May 22, 2019, which claims priorityunder 35 U.S.C. §119 to Japanese Patent Application No. 2018-124632,filed on Jun. 29, 2018. Each of the above applications is herebyexpressly incorporated by reference, in its entirety, into the presentapplication.

BACKGROUND OF THE INVENTION 1. Field of the Invention

The present invention relates to an ultrasound diagnostic apparatus andan operation method of an ultrasound diagnostic apparatus and inparticular, to an ultrasound diagnostic apparatus including a pluralityof ultrasound transducers, which are disposed inside a subject anddriven to transmit and receive ultrasound waves, and an operation methodof the ultrasound diagnostic apparatus.

2. Description of the Related Art

An ultrasound diagnostic apparatus that acquires an ultrasound image ofthe inside of a subject by transmitting and receiving ultrasound wavesby driving a plurality of ultrasound transducers inside the subject (forexample, inside the body of a patient) is already known. In theultrasound diagnostic apparatus described above, the plurality ofultrasound transducers are, for example, single crystal transducers thatare piezoelectric elements, and are usually used in a polarized state.The ultrasound transducer that is a single crystal transducer canreceive ultrasound waves with high sensitivity, but a depolarizationphenomenon in which the degree of polarization decreases as the drivingtime increases may occur. In a case where a depolarization phenomenonoccurs, the reception sensitivity of the ultrasound transducerdecreases, which may affect the image quality of the ultrasound image.

In particular, in the case of transmitting and receiving ultrasoundwaves by driving each ultrasound transducer inside the subject, since itis necessary to set the frequency of the ultrasound wave to a highfrequency band of 7 MHz to 8 MHz level, a transducer having a relativelysmall thickness is used. However, as the thickness of the transducerdecreases, the risk of occurrence of a depolarization phenomenonincreases.

For this reason, techniques for countermeasures against depolarizationin the ultrasound diagnostic apparatus have been developed so far. Forexample, an ultrasound diagnostic apparatus (referred to as a“piezoelectric sensor apparatus” in JP2013-005137A) described inJP2013-005137A has a piezoelectric element having a piezoelectric bodyand a pair of electrodes interposing the piezoelectric bodytherebetween, a detection circuit for performing detection processingfor detecting a detection signal output from the piezoelectric element,and a polarization processing circuit for performing polarizationprocessing by applying a polarization voltage to the piezoelectricelement. In the ultrasound diagnostic apparatus described inJP2013-005137A having such a configuration, polarization processing isperformed at a timing at which the electric power is supplied, a timingat which a request signal for executing detection processing is input(each reception timing), or a timing at which a predetermined standbytransition time has passed after the end of detection processing, forexample. Therefore, even in a case where a depolarization phenomenonoccurs in the piezoelectric element, the piezoelectric element can bepolarized again. As a result, it is possible to maintain the receptionsensitivity of the piezoelectric element.

As another example, an ultrasound diagnostic apparatus (referred to as a“piezoelectric sensor apparatus” in JP2013-161955A) described inJP2013-161955A has a piezoelectric element, a polarization checkingelement for checking the polarization state of the piezoelectricelement, a polarization processing unit for performing polarizationprocessing by applying a polarization voltage to the piezoelectricelement, and a controller for controlling the polarization timing of thepolarization processing unit. In a case where the apparatus power isturned on, the controller acquires a characteristic value correspondingto the amount of polarization of the polarization checking element,determines whether or not the polarization characteristic of thepiezoelectric element is unstable based on the characteristic value, andcauses the polarization processing unit to perform polarizationprocessing in a case where it is determined that the piezoelectricelement is unstable. Therefore, even in a case where the polarizationcharacteristic of the piezoelectric element becomes unstable, thepiezoelectric element is subjected to polarization processing. As aresult, since it is possible to return the polarization characteristicof the piezoelectric element to a state before degradation, it ispossible to prevent the performance of the ultrasound diagnosticapparatus from lowering.

In the ultrasound diagnostic apparatus described in each ofJP2013-005137A and JP2013-161955A, however, the timing at which thestate (depolarization) of the piezoelectric element is determined or thetiming of repolarization occurs is set to a predetermined timing, suchas a timing at which the electric power is supplied. Therefore, in theultrasound diagnostic apparatus described in each of JP2013-005137A andJP2013-161955A, it is necessary to wait for the above-described timingin order to restore the polarization of the piezoelectric element, andthis may cause the time required for the entire ultrasound diagnosis tobe excessively long.

In the ultrasound diagnostic apparatus described in JP2013-161955A, inorder to check the polarization state of the piezoelectric element, thepolarization checking element is separately provided. In such a case,since the piezoelectric checking element is provided, the size of theultrasound probe to be inserted into the patient’s body in the apparatusis increased. This may have an adverse effect on the operability (morespecifically, easiness of insertion into the body).

On the other hand, unlike the ultrasound diagnostic apparatusesdescribed in JP2013-005137A and JP2013-161955A, a technique capable ofdetermining the state of the piezoelectric element at a desired timinghas already been developed (for example, refer to JP2012-139460A).

The ultrasound diagnostic apparatus described in JP2012-139460A has anultrasound probe including a piezoelectric element, a storage unit forstoring a threshold value of a physical quantity (specifically, avoltage value of a reception signal) that changes with the degree ofdepolarization of the piezoelectric element, and a detection unit fordetecting the physical quantity in the ultrasound probe. In theultrasound diagnostic apparatus described in JP2012-139460A, forexample, in a case where the user operates a predetermined switch, thedetection result of the physical quantity is compared with the thresholdvalue stored in the storage unit. As described above, in the ultrasounddiagnostic apparatus described in JP2012-139460A, it is possible tocheck the polarization state of the piezoelectric element at the timingrequested by the user (specifically, at the time of switch operation).In addition, in the ultrasound diagnostic apparatus described inJP2012-139460A, unlike in the apparatus described in JP2013-161955A, apolarization checking element other than the piezoelectric element forultrasound diagnosis is not provided. Therefore, an increase in the sizeof the apparatus (specifically, an ultrasound probe) is suppressed.

The ultrasound diagnostic apparatus described in JP2012-139460A furtherhas a high voltage application unit that applies a high voltage forrepolarizing the piezoelectric element to the electrode of thepiezoelectric element. Then, in a case where the physical quantity isequal to or less than the threshold value, a control signal istransmitted to the high voltage application unit, and a high voltage forrepolarizing the piezoelectric element is applied to the electrode ofthe piezoelectric element. Therefore, in a case where the depolarizationof the piezoelectric element progresses and the performance of theultrasound probe is degraded, repolarization of the piezoelectricelement can be performed. As a result, it is possible to cope with thedepolarization of the piezoelectric element at an appropriate timing.

SUMMARY OF THE INVENTION

Incidentally, an ultrasound probe usually comprises a plurality ofultrasound transducers having piezoelectric elements. In addition, aphysical quantity that changes with the degree of depolarization of theultrasound transducer, for example, the voltage of the reception signal,tends to be different between elements because the driving time isdifferent between the elements and the like. Therefore, in the case ofdetermining the polarization state of the ultrasound transducer usingthe physical quantity (in other words, in the case of determiningwhether or not the polarization of the ultrasound transducer isrequired), it is necessary to take into consideration that theabove-described physical quantity varies between piezoelectric elements.In the ultrasound diagnostic apparatus described in JP2012-139460A,however, since such a variation in physical quantity is not taken intoconsideration, there is a possibility that an appropriate determinationresult on the necessity of polarization cannot be obtained.

The invention has been made in view of the aforementioned circumstances,and it is an object of the invention to achieve the following goal. Thatis, it is an object of the invention to provide an ultrasound diagnosticapparatus and an operation method of an ultrasound diagnostic apparatuscapable of obtaining an appropriate determination result on thenecessity of polarization of ultrasound transducers even in a case wherethe degree of depolarization varies between the ultrasound transducersby solving the aforementioned problems in the related art.

In order to achieve the aforementioned object, an ultrasound diagnosticapparatus of the invention comprises: an ultrasound transducer unit thatcomprises a plurality of ultrasound transducers and transmits andreceives ultrasound waves by driving driving target transducers, amongthe plurality of ultrasound transducers, inside a subject; a drivingvoltage supply unit that supplies a driving voltage to the drivingtarget transducers; a checking operation unit that is operated to checka state of the ultrasound transducer unit; a controller that controlsthe driving voltage supply unit such that the driving voltage issupplied to each of the plurality of ultrasound transducers with all ofthe plurality of ultrasound transducers as the driving targettransducers in a case where the checking operation unit is operated; adepolarization determination unit that, in a case where the checkingoperation unit is operated, calculates, for each ultrasound transducer,a reception sensitivity in a case where the ultrasound transducer unitreceives an ultrasound wave with all of the plurality of ultrasoundtransducers as the driving target transducers, and determines whether ornot a depolarization determination value calculated from the receptionsensitivity of each ultrasound transducer satisfies numerical conditionsset for the depolarization determination value; and a polarizationvoltage supply unit that supplies a polarization voltage to each of theplurality of ultrasound transducers in a case where the depolarizationdetermination unit determines that the depolarization determinationvalue satisfies the numerical conditions.

In the ultrasound diagnostic apparatus described above, it is preferablethat the depolarization determination unit calculates at least one of avariance of the reception sensitivity of each ultrasound transducer, anaverage value of the reception sensitivity of each ultrasoundtransducer, or a minimum value of the reception sensitivity of eachultrasound transducer as the depolarization determination value.

In the ultrasound diagnostic apparatus described above, it is preferablethat the ultrasound diagnostic apparatus further comprises a memory thatstores a cumulative value of a driving time of the driving targettransducer and that, in a case where the cumulative value stored in thememory is equal to or greater than a threshold value, the polarizationvoltage supply unit supplies the polarization voltage to each of theplurality of ultrasound transducers. In the ultrasound diagnosticapparatus described above, it is preferable that the cumulative valuestored in the memory is set to an initial value after the polarizationvoltage supply unit supplies the polarization voltage to each of theplurality of ultrasound transducers. In the ultrasound diagnosticapparatus described above, it is preferable that a console is providedto receive a user’s input operation regarding the threshold value. Inthe ultrasound diagnostic apparatus described above, it is preferablethat the ultrasound transducer unit and the memory are provided in anultrasound endoscope inserted into the subject. In the ultrasounddiagnostic apparatus described above, it is preferable that the checkingoperation unit is provided in the ultrasound endoscope. In theultrasound diagnostic apparatus described above, it is preferable thatthe ultrasound transducer unit is a convex type probe in which theplurality of ultrasound transducers are disposed in an arc shape.

In the ultrasound diagnostic apparatus described above, it is preferablethat an operation mode of the ultrasound diagnostic apparatus includes afirst mode and a second mode, the ultrasound transducer unit transmitsand receives ultrasound waves to and from an inside of the subject whilethe operation mode is the first mode, the ultrasound transducer unit islocated outside the subject while the operation mode is the second mode,the checking operation unit is operated while the operation mode is thesecond mode, and the polarization voltage supply unit supplies thepolarization voltage to each of the plurality of ultrasound transducerswhile the operation mode is the second mode.

In the ultrasound diagnostic apparatus described above, the ultrasoundtransducer unit may have an acoustic matching layer disposed outside theplurality of ultrasound transducers. In a case where the checkingoperation unit is operated, the controller may control the drivingvoltage supply unit such that the ultrasound transducer unit transmitsultrasound waves with all of the plurality of ultrasound transducers asthe driving target transducers and receive ultrasound waves reflected bythe acoustic matching layer. Alternatively, in the ultrasound diagnosticapparatus described above, the checking operation unit may be operatedin a state in which the ultrasound transducer unit is in contact with aphantom disposed outside the subject. In a case where the checkingoperation unit is operated, the controller may control the drivingvoltage supply unit such that the ultrasound transducer unit transmitsultrasound waves with all of the plurality of ultrasound transducers asthe driving target transducers and receive ultrasound waves reflected bythe phantom.

In addition, in order to achieve the object described above, anoperation method of an ultrasound diagnostic apparatus of the inventioncomprises: by using an ultrasound transducer unit comprising a pluralityof ultrasound transducers, transmitting and receiving ultrasound wavesby driving driving target transducers, among the plurality of ultrasoundtransducers, inside a subject; by using a driving voltage supply unit,supplying a driving voltage to the driving target transducers; operatinga checking operation unit to check a state of the ultrasound transducerunit; by using a controller, controlling the driving voltage supply unitsuch that the driving voltage is supplied to each of the plurality ofultrasound transducers with all of the plurality of ultrasoundtransducers as the driving target transducers in a case where thechecking operation unit is operated; by using a depolarizationdetermination unit, in a case where the checking operation unit isoperated, calculating, for each ultrasound transducer, a receptionsensitivity in a case where the ultrasound transducer unit receives anultrasound wave with all of the plurality of ultrasound transducers asthe driving target transducers, and determining whether or not adepolarization determination value calculated from the receptionsensitivity of each ultrasound transducer satisfies numerical conditionsset for the depolarization determination value; and by using apolarization voltage supply unit, supplying a polarization voltage toeach of the plurality of ultrasound transducers in a case where thedepolarization determination unit determines that the depolarizationdetermination value satisfies the numerical conditions.

According to the ultrasound diagnostic apparatus and the operationmethod of the ultrasound diagnostic apparatus of the invention, even ina case where the degree of depolarization varies between ultrasoundtransducers, it is possible to obtain an appropriate determinationresult on the necessity of polarization of ultrasound transducers.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 is a diagram showing the schematic configuration of an ultrasounddiagnostic apparatus according to an embodiment of the invention.

FIG. 2 is a plan view showing a distal end portion of an insertion partof an ultrasound endoscope and its periphery.

FIG. 3 is a diagram showing a cross section of the distal end portion ofthe insertion part of the ultrasound endoscope taken along the line I-Iin FIG. 2 .

FIG. 4 is a block diagram showing the configurations of an ultrasoundendoscope and an ultrasound processor apparatus.

FIG. 5 is a diagram showing the flow of a diagnostic process using theultrasound diagnostic apparatus.

FIG. 6 is a diagram showing the procedure of a diagnostic step in thediagnostic process.

FIG. 7 is a diagram showing the procedure of a scope checking step inthe diagnostic process.

FIG. 8A is a diagram showing the reception sensitivity of eachultrasound transducer (first example).

FIG. 8B is a diagram showing the reception sensitivity of eachultrasound transducer (second example).

FIG. 9 is a block diagram showing the configurations of an ultrasoundendoscope and an ultrasound processor apparatus according to a secondembodiment.

FIG. 10 is an explanatory diagram of a state checking scan in a thirdembodiment.

FIG. 11 is a block diagram showing the configuration of an ultrasoundprocessor apparatus according to a fourth embodiment.

FIG. 12 is a diagram showing the waveform of a polarization voltagesupplied in the fourth embodiment.

DESCRIPTION OF THE PREFERRED EMBODIMENTS

An ultrasound diagnostic apparatus according to an embodiment (thepresent embodiment) of the invention will be described in detail belowwith reference to preferred embodiments shown in the accompanyingdiagrams. The present embodiment is a representative embodiment of theinvention, but is merely an example and does not limit the invention.

In addition, in this specification, the numerical range expressed byusing “~” means a range including numerical values described before andafter “~” as a lower limit and an upper limit.

Outline of Ultrasound Diagnostic Apparatus

The outline of an ultrasound diagnostic apparatus 10 according to thepresent embodiment will be described with reference to FIGS. 1 to 4 .FIG. 1 is a diagram showing the schematic configuration of ultrasounddiagnostic apparatus 10. FIG. 2 is an enlarged plan view showing adistal end portion of an insertion part 22 of an ultrasound endoscope 12and the periphery thereof. In FIG. 2 , for convenience of illustration,a balloon 37 to be described later is shown by a broken line. FIG. 3 isa diagram showing a cross section of a distal end portion 40 of theinsertion part 22 of the ultrasound endoscope 12 taken along the lineI-I in FIG. 2 . FIG. 4 is a block diagram showing the configurations ofthe ultrasound endoscope 12 and an ultrasound processor apparatus 14.

The ultrasound diagnostic apparatus 10 is an ultrasound endoscopesystem, and is used to observe (hereinafter, also referred to asultrasound diagnosis) the state of an observation target part in a bodyof a patient, who is a subject, using ultrasound waves. Here, theobservation target part is a part that is difficult to examine from thebody surface side (outside) of the patient, for example, a gallbladderor a pancreas. By using the ultrasound diagnostic apparatus 10, it ispossible to perform ultrasound diagnosis of the state of the observationtarget part and the presence or absence of an abnormality throughgastrointestinal tracts such as esophagus, stomach, duodenum, smallintestine, and large intestine which are body cavities of the patient.

As shown in FIG. 1 , the ultrasound diagnostic apparatus 10 has theultrasound endoscope 12, the ultrasound processor apparatus 14, anendoscope processor apparatus 16, a light source device 18, a monitor20, and a console 100. As shown in FIG. 1 , a water supply tank 21 a, asuction pump 21 b, and an air supply pump 21 c are provided asaccessories of the ultrasound diagnostic apparatus 10. In addition, apipe line (not shown) serving as a flow path of water and gas is formedin the ultrasound endoscope 12.

The ultrasound endoscope 12 is an endoscope, and as shown in FIG. 1 ,has the insertion part 22 to be inserted into the body cavity of apatient and an operation unit 24 operated by an operator (user), such asa doctor or a technician. In addition, as shown in FIGS. 2 and 3 , anultrasound transducer unit 46 comprising a plurality of ultrasoundtransducers 48 is attached to the distal end portion 40 of the insertionpart 22.

By the function of the ultrasound endoscope 12, the operator can acquirean endoscope image of the inner wall of the body cavity of the patientand an ultrasound image of the observation target part. The endoscopeimage is an image obtained by imaging the inner wall of the body cavityof the patient using an optical method. The ultrasound image is an imageobtained by receiving a reflected wave (echo) of an ultrasound wavetransmitted from the inside of the body cavity of the patient to theobservation target part and imaging the reception signal. The ultrasoundendoscope 12 will be described in detail later.

As shown in FIG. 1 , the ultrasound processor apparatus 14 is connectedto the ultrasound endoscope 12 through a universal cord 26 and anultrasound connector 32 a provided at an end portion of the universalcord 26. The ultrasound processor apparatus 14 controls the ultrasoundtransducer unit 46 of the ultrasound endoscope 12 to transmit theultrasound wave to the ultrasound transducer unit 46. In addition, theultrasound processor apparatus 14 generates an ultrasound image byimaging the reception signal in a case where the reflected wave (echo)of the ultrasound wave is received by the ultrasound transducer unit 46.The ultrasound processor apparatus 14 will be described in detail later.

As shown in FIG. 1 , the endoscope processor apparatus 16 is connectedto the ultrasound endoscope 12 through the universal cord 26 and anendoscope connector 32 b provided at an end portion of the universalcord 26. The endoscope processor apparatus 16 generates an endoscopeimage by acquiring image data of an observation target adjacent partimaged by the ultrasound endoscope 12 (more specifically, a solid-stateimaging element 86 to be described later) and performing predeterminedimage processing on the acquired image data. The observation targetadjacent part is a portion of the inner wall of the body cavity of thepatient that is adjacent to the observation target part.

As shown in FIG. 1 , the light source device 18 is connected to theultrasound endoscope 12 through the universal cord 26 and a light sourceconnector 32 c provided at an end portion of the universal cord 26. Thelight source device 18 emits white light or specific wavelength lightformed of three primary color light components of red light, greenlight, and blue light at the time of imaging the observation targetadjacent part using the ultrasound endoscope 12. The light emitted fromthe light source device 18 propagates through the ultrasound endoscope12 through a light guide (not shown) included in the universal cord 26,and is emitted from the ultrasound endoscope 12 (more specifically, anillumination window 88 to be described later). As a result, theobservation target adjacent part is illuminated with the light from thelight source device 18.

In the present embodiment, the ultrasound processor apparatus 14 and theendoscope processor apparatus 16 are formed by two apparatuses(computers) provided separately. However, the invention is not limitedthereto, and both the ultrasound processor apparatus 14 and theendoscope processor apparatus 16 may be formed by one apparatus.

As shown in FIG. 1 , the monitor 20 is connected to the ultrasoundprocessor apparatus 14, and the endoscope processor apparatus 16, anddisplays an ultrasound image generated by the ultrasound processorapparatus 14 and an endoscope image generated by the endoscope processorapparatus 16. Regarding the display of the ultrasound image and theendoscope image, either one of the images may be switched and displayedon the monitor 20, or both the images may be displayed at the same time.A configuration may be adopted in which these display methods can befreely selected and changed. In the present embodiment, the ultrasoundimage and the endoscope image are displayed on one monitor 20. However,a monitor for displaying the ultrasound image and a monitor fordisplaying the endoscope image may be separately provided. In addition,the ultrasound image and the endoscope image may be displayed in adisplay form other than the monitor 20. For example, the ultrasoundimage and the endoscope image may be displayed on a display of apersonal terminal carried by the operator.

The console 100 is an input device provided for the operator to inputinformation necessary for ultrasound diagnosis or for the operator toinstruct the ultrasound processor apparatus 14 to start ultrasounddiagnosis. The console 100 is configured to include, for example, akeyboard, a mouse, a trackball, a touch pad, and a touch panel, and isconnected to a CPU 152 of the ultrasound processor apparatus 14 as shownin FIG. 4 . In a case where the console 100 is operated, the CPU 152 ofthe ultrasound processor apparatus 14 controls each unit of theapparatus (for example, a reception circuit 142 and a transmissioncircuit 144 to be described later) according to the operation content.

Specifically, the operator inputs examination information (for example,examination order information including a date and an order number andpatient information including a patient ID and a patient name) throughthe console 100 before starting the ultrasound diagnosis. In a casewhere the operator gives an instruction to start the ultrasounddiagnosis through the console 100 after the input of the examinationinformation is completed, the CPU 152 of the ultrasound processorapparatus 14 controls each unit of the ultrasound processor apparatus 14so that the ultrasound diagnosis is performed based on the inputexamination information.

The operator can set various control parameters with the console 100 atthe time of performing the ultrasound diagnosis. As the controlparameters, for example, selection results of a live mode and a freezemode, set values of the display depth (depth), selection results of anultrasound image generation mode, and the like can be mentioned. Here,the “live mode” is a mode in which ultrasound images (moving images)obtained at a predetermined frame rate are sequentially displayed(displayed in real time). The “freeze mode” is a mode in which anultrasound image (still image) of one frame acquired in the past is readout from a cine memory 150 to be described later and displayed.

There are a plurality of ultrasound image generation modes that can beselected in the present embodiment. Specifically, there are a brightness(B) mode, a color flow (CF) mode, and a pulse wave (PW) mode. The B modeis a mode in which a tomographic image is displayed by converting theamplitude of the ultrasound echo into a brightness. The CF mode is amode in which average blood flow speed, flow fluctuation, strength offlow signal, flow power, and the like are mapped to various colors anddisplayed so as to be superimposed on a B mode image. The PW mode is amode in which the speed (for example, blood flow speed) of theultrasound echo source detected based on the transmission and receptionof the pulse wave is displayed. The ultrasound image generation modesdescribed above are merely examples, and modes other than theabove-described three kinds of modes, for example, an amplitude (A) modeand a motion (M) mode may be further included.

In the present embodiment, a checking operation unit 102 and a thresholdvalue input unit 104 are provided in the console 100 as shown in FIG. 4. The checking operation unit 102 is a unit operated by the operator inorder to check the state of the ultrasound endoscope 12, in particular,the state of the ultrasound transducer unit 46. Here, the state of theultrasound transducer unit 46 is a state relevant to the performance ofthe ultrasound transducer unit 46, specifically, the degree of progressof depolarization of the ultrasound transducer unit 46. The checkingoperation unit 102 may be a physical push button or switch provided inthe console 100, or may be a button image drawn on the display screen ofthe console 100 in a case where the console 100 is formed by a touch pador a touch panel.

The threshold value input unit 104 is a unit operated by the operator inorder to set a threshold value used for determining whether or notpolarization processing is required, which will be described later. Thatis, the console 100 comprising the threshold value input unit 104receives an input operation of the operator regarding theabove-described threshold value. The threshold value input unit 104 maybe formed by a keyboard, a numeric keypad, or a mouse provided in theconsole 100. Alternatively, the threshold value input unit 104 may beformed by an input window or an input box drawn on the display screen ofthe console 100 in a case where the console 100 is formed by a touch pador a touch panel.

In the ultrasound diagnostic apparatus 10 configured as described above,in a case where the electric power is supplied, the operator firstoperates the console 100 to input the above-described examinationinformation.

In a case where the operator gives an instruction to start theultrasound diagnosis through the console 100 after the input of theexamination information is completed, the operation mode of theultrasound diagnostic apparatus 10 (hereinafter, simply referred to asan operation mode) is switched to the first mode. Thereafter, theoperator inserts the insertion part 22 of the ultrasound endoscope 12into the body cavity of the patient. As a result, a plurality ofultrasound transducers 48 provided in the ultrasound transducer unit 46are disposed in the body cavity of the patient. While the operation modeis the first mode, a diagnostic step is performed. In the diagnosticstep, ultrasound diagnosis is performed by the ultrasound diagnosticapparatus 10. That is, while the operation mode is the first mode, eachof the ultrasound image and the endoscope image is acquired according tothe examination information.

On the other hand, until the operator gives an instruction to start theultrasound diagnosis after the electric power is supplied, the operationmode is set to the second mode. In the present embodiment, while theoperation mode is the second mode, the ultrasound endoscope 12 includingthe ultrasound transducer unit 46 is located outside the body cavity ofthe patient (that is, outside the patient). Then, while the operationmode is the second mode, a scope checking step is performed. In thescope checking step, the state of the ultrasound endoscope 12, inparticular, the state of the ultrasound transducer unit 46 is checked,and the necessity of polarization of the ultrasound transducer 48 isdetermined from the checking result. In a case where the determinationresult that the polarization is required is obtained, the ultrasoundprocessor apparatus 14 performs polarization processing for polarizing(repolarizing) the ultrasound transducer 48.

The polarization processing is processing for polarizing (repolarizing)the ultrasound transducer 48 by supplying a polarization voltage to theultrasound transducer 48. By performing the polarization processing, thedepolarized ultrasound transducer 48 can be polarized again by repeatingthe ultrasound diagnosis. As a result, it is possible to restore thereception sensitivity of the ultrasound transducer 48 with respect toultrasound waves to a satisfactory level.

As described above, in the present embodiment, the operation modeincludes the first mode and the second mode. However, the operation modeis not limited to the above-described modes, and may include at leastthe first mode and the second mode, and modes (for example, a mode formaintenance of each unit of the ultrasound diagnostic apparatus 10)other than the above-described modes may be further included.

Configuration of Ultrasound Endoscope

Next, the configuration of the ultrasound endoscope 12 will be describedwith reference to FIGS. 1 to 4 . As shown in FIG. 1 , the ultrasoundendoscope 12 has the insertion part 22 and the operation unit 24. Asshown in FIG. 1 , the insertion part 22 comprises the distal end portion40, a bending portion 42, and a flexible portion 43 in order from thedistal end side (free end side). As shown in FIG. 2 , an ultrasoundobservation portion 36 and an endoscope observation portion 38 areprovided in the distal end portion 40.

As shown in FIGS. 2 and 3 , a treatment tool lead-out port 44 isprovided in the distal end portion 40. The treatment tool lead-out port44 serves as an outlet of a treatment tool (not shown), such as forceps,an insertion needle, or a high frequency scalpel, and also serves as asuction port for sucking aspirates, such as blood and body waste.

As shown in FIG. 2 , a cleaning nozzle 90 formed to clean the surfacesof an observation window 82 and the illumination window 88 is providedin the distal end portion 40. Air or cleaning liquid is ejected from thecleaning nozzle 90 toward the observation window 82 and the illuminationwindow 88.

As shown in FIGS. 1 and 2 , a balloon 37 that can expand and contract isattached to the distal end portion 40 at a position covering theultrasound transducer unit 46. The balloon 37 can be inserted into thebody cavity of the patient together with the ultrasound transducer unit46. Then, water (specifically, degassed water) as an ultrasoundtransmission medium is injected into the balloon 37 from a water supplyport 47 formed near the ultrasound transducer unit 46 in the distal endportion 40. As a result, the balloon 37 expands. In a case where theexpanded balloon 37 comes in contact with the inner wall of the bodycavity (for example, the periphery of the observation target adjacentpart), air between the ultrasound transducer unit 46 and inner wall ofthe body cavity is eliminated. Therefore, it is possible to preventattenuation of ultrasound waves and reflected waves (echoes) thereof inthe air.

As shown in FIG. 1 , the bending portion 42 is a portion provided on themore proximal side (side opposite to the side where the ultrasoundtransducer unit 46 is provided) than the distal end portion 40 in theinsertion part 22, and can bend freely. As shown in FIG. 1 , theflexible portion 43 is a portion connecting the bending portion 42 andthe operation unit 24 to each other, has flexibility, and is provided soas to extend in an elongated state.

As shown in FIG. 1 , a pair of angle knobs 29 and a treatment toolinsertion port 30 are provided in the operation unit 24. In a case whereeach angle knob 29 is rotated, the bending portion 42 is remotelyoperated to be bent and deformed. By this deformation operation, thedistal end portion 40 of the insertion part 22 in which the ultrasoundobservation portion 36 and the endoscope observation portion 38 areprovided can be directed in a desired direction. The treatment toolinsertion port 30 is a hole formed to insert a treatment tool, such asforceps, and communicates with the treatment tool lead-out port 44through a treatment tool channel 45 (refer to FIG. 3 ).

As shown in FIG. 1 , an air and water supply button 28 a for opening andclosing an air and water supply pipe line (not shown) extending from thewater supply tank 21 a, and a suction button 28 b for opening andclosing a suction pipe line (not shown) extending from the suction pump21 b are provided in the operation unit 24. Gas, such as air sent fromthe air supply pump 21 c and water in the water supply tank 21 a flowthrough the air and water supply pipe line. In a case where the air andwater supply button 28 a is operated, a portion to be opened in the airand water supply pipe line is switched, and gas and water injectionports are also switched between the cleaning nozzle 90 and the watersupply port 47 in a corresponding manner. That is, it is possible toselectively perform cleaning of the endoscope observation portion 38 andexpansion of the balloon 37 by operating the air and water supply button28 a.

The suction pipe line is provided to suck an aspirate in the body cavitysucked from the cleaning nozzle 90 or to suck water in the balloon 37through the water supply port 47. In a case where the suction button 28b is operated, a portion to be opened in the suction pipe line isswitched, and a suction port is also switched between the cleaningnozzle 90 and the water supply port 47 in a corresponding manner. Thatis, a target object to be sucked by the suction pump 21 b can beswitched by operating the suction button 28 b.

As shown in FIG. 1 , the ultrasound connector 32 a connected to theultrasound processor apparatus 14, the endoscope connector 32 bconnected to the endoscope processor apparatus 16, and the light sourceconnector 32 c connected to the light source device 18 are provided inthe other end portion of the universal cord 26. The ultrasound endoscope12 is detachably connected to the ultrasound processor apparatus 14, theendoscope processor apparatus 16, and the light source device 18 throughthe connectors 32 a, 32 b, and 32 c, respectively.

Next, the ultrasound observation portion 36 and the endoscopeobservation portion 38 among the components of the ultrasound endoscope12 will be described in detail.

Ultrasound Observation Portion

The ultrasound observation portion 36 is a portion provided to acquirean ultrasound image, and is disposed on the distal end side in thedistal end portion 40 of the insertion part 22 as shown in FIGS. 2 and 3. As shown in FIG. 3 , the ultrasound observation portion 36 comprisesthe ultrasound transducer unit 46, a plurality of coaxial cables 56, anda flexible printed circuit (FPC) 60.

The ultrasound transducer unit 46 corresponds to an ultrasound probe(probe), and transmits and receives ultrasound waves in the body cavityof the patient (inside the subject). Specifically, the ultrasoundtransducer unit 46 transmits and receives ultrasound waves by driving adriving target transducer, among the plurality of ultrasound transducers48, in the body cavity of the patient. The driving target transducer isthe ultrasound transducer 48 that is actually driven (vibrated) at thetime of ultrasound diagnosis to emit an ultrasound wave and outputs areception signal that is an electric signal at the time of receiving thereflected wave (echo). In the present embodiment, the ultrasoundtransducer unit 46 is integrated with the endoscope, so that theultrasound transducer unit 46 is inserted into the body cavity of thepatient together with the endoscope. However, the invention is notlimited thereto. For example, the ultrasound transducer unit 46 may beseparated from the endoscope, so that the ultrasound transducer unit 46is inserted into the body cavity of the patient separately from theendoscope.

As shown in FIG. 3 , the ultrasound transducer unit 46 according to thepresent embodiment is a convex type probe in which a plurality ofultrasound transducers 48 are disposed in an arc shape, and transmitsultrasound waves in a radial shape (arc shape). However, the type(model) of the ultrasound transducer unit 46 is not particularlylimited, and other types may be used as long as it is possible totransmit and receive ultrasound waves. For example, a sector type, alinear type, and a radial type may be used.

As shown in FIG. 3 , the ultrasound transducer unit 46 is formed bylaminating a backing material layer 54, an ultrasound transducer array50, an acoustic matching layer 76, and an acoustic lens 78.

The ultrasound transducer array 50 includes a plurality of ultrasoundtransducers 48 (ultrasound transducers) arranged in a one-dimensionalarray as shown in FIG. 3 . More specifically, the ultrasound transducerarray 50 is formed by arranging N (for example, N = 128) ultrasoundtransducers 48 at equal intervals in a convex bending shape along theaxial direction of the distal end portion 40 (longitudinal axisdirection of the insertion part 22). The ultrasound transducer array 50may be one in which a plurality of ultrasound transducers 48 aredisposed in a two-dimensional array.

Each of the N ultrasound transducers 48 is formed by disposingelectrodes on both surfaces of a single crystal transducer that is apiezoelectric element. As the single crystal transducer, any of quartz,lithium niobate, lead magnesium niobate (PMN), lead zinc niobate (PZN),lead indium niobate (PIN), lead titanate (PT), lithium tantalate,langasite, and zinc oxide can be used. The electrodes is an individualelectrode (not shown) individually provided for each of the plurality ofultrasound transducers 48 and a ground electrode (not shown) common tothe plurality of ultrasound transducers 48. In addition, the electrodesare electrically connected to the ultrasound processor apparatus 14through the coaxial cable 56 and the FPC 60.

The ultrasound transducer 48 according to the present embodiment needsto be driven (vibrated) at a relatively high frequency of 7 MHz to 8 MHzlevel in order to acquire an ultrasound image in the body cavity of thepatient. For this reason, the thickness of the piezoelectric elementforming the ultrasound transducer 48 is designed to be relatively small.For example, the thickness of the piezoelectric element forming theultrasound transducer 48 is 75 µm to 125 µm, preferably 90 µm to 125 µm.

A pulsed driving voltage is supplied from the ultrasound processorapparatus 14 to each ultrasound transducer 48, as an input signal,through the coaxial cable 56. In a case where the driving voltage isapplied to the electrodes of the ultrasound transducer 48, thepiezoelectric element expands and contracts to drive (vibrate) theultrasound transducer 48. As a result, a pulsed ultrasound wave isoutput from the ultrasound transducer 48. In this case, the amplitude ofthe ultrasound wave output from the ultrasound transducer 48 has amagnitude corresponding to the intensity (output intensity) in a casewhere the ultrasound transducer 48 outputs the ultrasound wave. Here,the output intensity is defined as the magnitude of the sound pressureof the ultrasound wave output from the ultrasound transducer 48.

Each ultrasound transducer 48 vibrates (is driven) upon receiving thereflected wave (echo) of the ultrasound wave, and the piezoelectricelement of each ultrasound transducer 48 generates an electric signal.The electric signal is output from each ultrasound transducer 48 to theultrasound processor apparatus 14 as a reception signal of theultrasound wave. In this case, the magnitude (voltage value) of theelectric signal output from the ultrasound transducer 48 has a magnitudecorresponding to the reception sensitivity in a case where theultrasound transducer 48 receives the ultrasound wave. Here, thereception sensitivity is defined as a ratio of the amplitude of theelectric signal, which is output from the ultrasound transducer 48 inresponse to reception of the ultrasound wave, to the amplitude of theultrasound wave transmitted by the ultrasound transducer 48.

As described above, the ultrasound transducer unit 46 of the presentembodiment is a convex type. That is, in the present embodiment, bysequentially driving the N ultrasound transducers 48 provided in theultrasound transducer unit 46 with an electronic switch such as amultiplexer 140, an ultrasound scan occurs in a scanning range along thecurved surface on which the ultrasound transducer array 50 is disposed,for example, in the range of about several tens of mm from the center ofcurvature of the curved surface.

More specifically, for example, in the case of acquiring a B mode image(tomographic image) as an ultrasound image, a driving voltage issupplied to m (for example, m = N/2) driving target transducers arrangedin series, among the N ultrasound transducers 48, by channel selectionof the multiplexer 140. As a result, each of the m driving targettransducers is driven, and an ultrasound wave from each of the drivingtarget transducers is output through the opening. The output multrasound waves are immediately synthesized, and the composite wave(ultrasound beam) is transmitted to the observation target part.Thereafter, each of the m driving target transducers receives anultrasound wave (echo) reflected at the observation target part, andoutputs an electric signal (reception signal) corresponding to thereception sensitivity at that point in time.

The above-described series of steps (that is, supply of a drivingvoltage, transmission and reception of ultrasound waves, and output ofan electric signal) are repeatedly performed while switching the openingchannel in the multiplexer 140 to shift the position of the drivingtarget transducer one by one (one ultrasound transducer 48 at a time).For example, in the case of acquiring a B mode image for one frame, theabove-described series of steps (hereinafter, referred to as a path forconvenience) are repeated a total of N times from the ultrasoundtransducer 48 on one end side toward the ultrasound transducer 48 on theother end side among the N ultrasound transducers 48, and each imagepiece forming the B mode image is formed by each path. Here, the imagepiece is obtained by dividing an approximately fan-shaped B mode imageinto N equal parts along an arc which is the outer edge thereof.

As shown in FIG. 3 , the backing material layer 54 supports theultrasound transducer array 50 from the back side (side opposite to theacoustic matching layer 76). In addition, the backing material layer 54has a function of attenuating ultrasound waves propagating to the backside of the ultrasound transducer array 50 among ultrasound wavesemitted from the ultrasound transducer 48 or ultrasound waves (echoes)reflected by the observation target part. The backing material is amaterial having rigidity, such as hard rubber, and an appropriate amountof ultrasound damping material (ferrite, ceramics, and the like) isadded.

The acoustic matching layer 76 is provided for acoustic impedancematching between the body of the patient and the driving targettransducer. The acoustic matching layer 76 is disposed outside theultrasound transducer array 50 (that is, outside the plurality ofultrasound transducers 48). Strictly speaking, the acoustic matchinglayer 76 is superimposed on the ultrasound transducer array 50 as shownin FIG. 3 . Since the acoustic matching layer 76 is provided, it ispossible to increase the transmittance of the ultrasound wave. As amaterial of the acoustic matching layer 76, it is possible to usevarious organic materials whose acoustic impedance values are closer tothat of the body of the patient than the piezoelectric element of theultrasound transducer 48. Specific examples of the material of theacoustic matching layer 76 include epoxy resin, silicone rubber,polyimide, polyethylene, and the like.

Some of the ultrasound waves transmitted from the driving targettransducers are reflected at the boundary position of the acoustic lens78 due to the difference in acoustic impedance. Therefore, theultrasound transducer unit 46 receives ultrasound waves reflected at theboundary position of the acoustic lens 78 with the driving targettransducers. At this time, each of the driving target transducersreceives the ultrasound wave with the reception sensitivity at thatpoint in time, and outputs the reception signal corresponding to thereception sensitivity.

The acoustic lens 78 converges the ultrasound waves emitted from thedriving target transducers toward the observation target part, and issuperimposed on the acoustic matching layer 76 as shown in FIG. 3 . Theacoustic lens 78 is formed of, for example, silicon resin (millablesilicone rubber (HTV rubber), liquid silicone rubber (RTV rubber), andthe like), butadiene resin, and polyurethane resin, and powders oftitanium oxide, alumina, silica, and the like are mixed as necessary.

The FPC 60 is electrically connected to the electrode of each ultrasoundtransducer 48. As shown in FIG. 3 , each of the plurality of coaxialcables 56 is wired to the FPC 60 at one end thereof. In a case where theultrasound endoscope 12 is connected to the ultrasound processorapparatus 14 through the ultrasound connector 32 a, each coaxial cable56 is electrically connected to the ultrasound processor apparatus 14 atthe other end (side opposite to the FPC 60).

As shown in FIG. 4 , the ultrasound endoscope 12 comprises a memory(hereinafter, referred to as an endoscope side memory 58). The endoscopeside memory 58 stores a cumulative value of the driving time of thedriving target transducer (that is, the total driving time) in a periodduring which the operation mode is the first mode. In the presentembodiment, it is assumed that the time from the operator’s instructionto start ultrasound diagnosis to the end of the ultrasound diagnosis(more specifically, the time during which ultrasound diagnosis isperformed in the live mode) is handled as the driving time. However, theinvention is not limited thereto, and the time during which the drivingvoltage is actually supplied to the driving target transducer may be thedriving time.

In a state in which the ultrasound endoscope 12 is connected to theultrasound processor apparatus 14, the CPU 152 of the ultrasoundprocessor apparatus 14 can access the endoscope side memory 58 to readthe cumulative value of the driving time stored in the endoscope sidememory 58. In addition, the CPU 152 of the ultrasound processorapparatus 14 rewrites (that is, clears) the cumulative value of thedriving time stored in the endoscope side memory 58 to an initial value,or updates the cumulative value of the driving time in a case where thecumulative value of the driving time increases with the execution of theultrasound diagnosis.

Endoscope Observation Portion

The endoscope observation portion 38 is a portion provided to acquire anendoscope image, and is disposed on the more proximal end side than theultrasound observation portion 36 in the distal end portion 40 of theinsertion part 22 as shown in FIGS. 2 and 3 . As shown in FIGS. 2 and 3, the endoscope observation portion 38 includes the observation window82, an objective lens 84, the solid-state imaging element 86, theillumination window 88, the cleaning nozzle 90, a wiring cable 92, andthe like.

As shown in FIG. 3 , the observation window 82 is attached so as to beinclined with respect to the axial direction (longitudinal axisdirection of the insertion part 22) at the distal end portion 40 of theinsertion part 22. Light incident through the observation window 82 andreflected at the observation target adjacent part is focused on theimaging surface of the solid-state imaging element 86 by the objectivelens 84.

The solid-state imaging element 86 photoelectrically converts thereflected light of the observation target adjacent part, which isfocused on the imaging surface after being transmitted through theobservation window 82 and the objective lens 84, and outputs an imagingsignal. As the solid-state imaging element 86, it is possible to use acharge coupled device (CCD), a complementary metal oxide semiconductor(CMOS), and the like. The captured image signal output from thesolid-state imaging element 86 is transmitted to the endoscope processorapparatus 16 by the universal cord 26 through the wiring cable 92extending from the insertion part 22 to the operation unit 24.

As shown in FIG. 2 , the illumination window 88 is provided at both sidepositions of the observation window 82. An exit end of a light guide(not shown) is connected to the illumination window 88. The light guideextends from the insertion part 22 to the operation unit 24, and itsincidence end is connected to the light source device 18 connectedthrough the universal cord 26. The illumination light emitted from thelight source device 18 is transmitted through the light guide and isemitted from the illumination window 88 toward the observation targetadjacent part.

Configuration of Ultrasound Processor Apparatus

The ultrasound processor apparatus 14 causes the ultrasound transducerunit 46 to transmit and receive ultrasound waves, and generates anultrasound image by converting the reception signal, which is outputfrom the driving target transducer at the time of ultrasound wavereception, into an image. In addition, the ultrasound processorapparatus 14 displays the generated ultrasound image on the monitor 20.

In the present embodiment, the ultrasound processor apparatus 14(strictly speaking, a polarization processing unit 155 to be describedbelow) performs polarization processing, and supplies a polarizationvoltage to each ultrasound transducer 48 to perform polarization(repolarization). By the execution of the polarization processing, thedepolarized ultrasound transducer 48 can be polarized again by repeatingthe ultrasound diagnosis. As a result, it is possible to restore thereception sensitivity of the ultrasound transducer 48 with respect toultrasound waves to a satisfactory level.

In the present embodiment, the polarization processing is performed in aperiod during which the ultrasound diagnosis is not performed,specifically, a period during which the operation mode is the secondmode. More specifically, the polarization processing is performed in thescope checking step.

As shown in FIG. 4 , the ultrasound processor apparatus 14 has themultiplexer 140, the reception circuit 142, the transmission circuit144, an A/D converter 146, an Application Specific Integrated Circuit(ASIC) 148, the cine memory 150, a memory controller 151, a centralprocessing unit (CPU) 152, a digital scan converter (DSC) 154, and thepolarization processing unit 155.

As shown in FIG. 4 , the reception circuit 142 and the transmissioncircuit 144 are electrically connected to the ultrasound transducerarray 50 of the ultrasound endoscope 12 through the multiplexer 140. Themultiplexer 140 selects a maximum of m driving target transducers fromthe N ultrasound transducers 48, and opens their channels.

The transmission circuit 144 forms a driving voltage supply unit, and isa circuit that supplies a driving voltage for ultrasound wavetransmission to the driving target transducers selected by themultiplexer 140 in order to transmit ultrasound waves from theultrasound transducer unit 46. The driving voltage is a pulsed voltagesignal, and is applied to the electrodes of the driving targettransducers through the universal cord 26 and the coaxial cable 56.

The reception circuit 142 is a circuit that receives an electric signaloutput from the driving target transducer that has received anultrasound wave (echo), that is, a reception signal. In addition,according to the control signal transmitted from the CPU 152, thereception circuit 142 amplifies the reception signal received from theultrasound transducer 48 and transmits the amplified signal to the A/Dconverter 146. As shown in FIG. 4 , the A/D converter 146 is connectedto the reception circuit 142, and converts the reception signal receivedfrom the reception circuit 142 from an analog signal to a digital signaland outputs the converted digital signal to the ASIC 148.

As shown in FIG. 4 , the ASIC 148 is connected to the A/D converter 146.As shown in FIG. 4 , the ASIC 148 forms a phase matching unit 160, a Bmode image generation unit 162, a PW mode image generation unit 164, aCF mode image generation unit 166, and a depolarization determinationunit 170. In the present embodiment, the above-described functions(specifically, the phase matching unit 160, the B mode image generationunit 162, the PW mode image generation unit 164, the CF mode imagegeneration unit 166, and the depolarization determination unit 170) arerealized by a hardware circuit, such as the ASIC 148. However, theinvention is not limited thereto. The above-described functions may berealized by making the central processing unit (CPU) and software(computer program) for executing various kinds of data processingcooperate with each other.

The phase matching unit 160 performs processing for phasing addition(addition after matching the phases of reception data) by giving a delaytime to the reception signal (reception data) digitized by the A/Dconverter 146. By the phasing addition processing, a sound ray signalwith narrowed focus of the ultrasound echo is generated.

The B mode image generation unit 162, the PW mode image generation unit164, and the CF mode image generation unit 166 generate an ultrasoundimage based on the electric signal (strictly speaking, the sound raysignal generated by phasing and adding the reception data) that isoutput from the driving target transducer among the plurality ofultrasound transducers 48 in a case where the ultrasound transducer unit46 receives the ultrasound wave.

The B mode image generation unit 162 generates a B mode image that is atomographic image of the inside of the patient (inside of the bodycavity). For the sequentially generated sound ray signals, the B modeimage generation unit 162 corrects the attenuation due to thepropagation distance according to the depth of the reflection positionof the ultrasound wave by sensitivity time gain control (STC). The Bmode image generation unit 162 performs envelope detection processingand logarithm (Log) compression processing on the corrected sound raysignal, thereby generating a B mode image (image signal).

The PW mode image generation unit 164 generates an image showing theblood flow speed in a predetermined direction. The PW mode imagegeneration unit 164 extracts a frequency component by applying a fastFourier transform to a plurality of sound ray signals in the samedirection among the sound ray signals sequentially generated by thephase matching unit 160. Thereafter, the PW mode image generation unit164 calculates the blood flow speed from the extracted frequencycomponent, and generates a PW mode image (image signal) showing thecalculated blood flow speed.

The CF mode image generation unit 166 generates an image showing bloodflow information in a predetermined direction. The CF mode imagegeneration unit 166 generates an image signal indicating the blood flowinformation by calculating the autocorrelation between a plurality ofsound ray signals in the same direction among the sound ray signalssequentially generated by the phase matching unit 160. Thereafter, theCF mode image generation unit 166 generates a CF mode image (imagesignal) as a color image on which the blood flow information issuperimposed by including the image signal in the B mode image signal.

The number of ultrasound transducers 48 as driving target transducers ineach image forming mode, the driving frequency, and the like aredetermined according to the type of the ultrasound image forming mode.For example, in order to generate an image for one frame (B mode image)in the B mode, all of the N ultrasound transducers 48 are used asdriving target transducers. However, among the N ultrasound transducers48, the driving frequency in the ultrasound transducer 48 on the endside is higher than that in the ultrasound transducer 48 in the vicinityof the center.

In the PW mode, since the ultrasound transducer 48 corresponding to thedirection designated by the operator is used as a driving targettransducer, the driving frequency of the ultrasound transducer 48 ishigher than the driving frequency of the other ultrasound transducers48. In the CF mode, in the case of generating the above-described colorimage (CF mode image), all of the N ultrasound transducers 48 are usedas driving target transducers, but a larger number of ultrasoundtransducers 48 corresponding to the direction designated by the operatorare driven. Therefore, in the CF mode, the driving frequency in theultrasound transducer 48 on the end side is higher than that in theultrasound transducer 48 in the vicinity of the center, and the drivingfrequency of the ultrasound transducer 48 corresponding to the directiondesignated by the operator is higher than the driving frequency of theother ultrasound transducers 48.

As described above, the number of driving target transducers and thedriving frequency are changed according to the type of the ultrasoundimage forming mode. Due to this, the driving frequency (in other words,the driving time) of each ultrasound transducer 48 varies between theultrasound transducers 48. As the driving time passes, depolarizationproceeds in the ultrasound transducer 48. That is, the variation in thedriving time between the ultrasound transducers 48 means that the degreeof progress of depolarization varies between the ultrasound transducers48.

The depolarization determination unit 170 determines the state of theultrasound transducer unit 46, specifically, the degree of progress ofdepolarization of the ultrasound transducer 48. In the case ofdetermining the degree of progress of depolarization, the depolarizationdetermination unit 170 calculates a depolarization determination valuethat is an index value. In addition, the depolarization determinationunit 170 determines whether or not the calculated depolarizationdetermination value satisfies numerical conditions. The numericalconditions are set for the depolarization determination value, and arerecorded on the ultrasound processor apparatus 14 side. As shown in FIG.4 , the depolarization determination unit 170 is connected to the CPU152. In a case where it is determined that the depolarizationdetermination value satisfies the numerical conditions, thedepolarization determination unit 170 transmits the determination resultto the CPU 152. The series of processing by the depolarizationdetermination unit 170 (calculation of the depolarization determinationvalue and condition determination regarding the depolarizationdetermination value) will be described in detail in the “Operationexample of the ultrasound diagnostic apparatus” later.

As shown in FIG. 4 , the DSC 154 is connected to the ASIC 148, andconverts (raster conversion) the signal of the image generated by the Bmode image generation unit 162, the PW mode image generation unit 164,or the CF mode image generation unit 166 into an image signal accordingto a normal television signal scanning method, performs various kinds ofrequired image processing, such as gradation processing, on the imagesignal, and then outputs an obtained signal to the monitor 20.

The memory controller 151 stores the image signal generated by the Bmode image generation unit 162, the PW mode image generation unit 164,or the CF mode image generation unit 166 in the cine memory 150. Thecine memory 150 has a capacity for storing an image signal for one frameor several frames. The image signal generated by the ASIC 148 is outputto the DSC 154, and is also stored in the cine memory 150 by the memorycontroller 151. In the freeze mode, the memory controller 151 reads theimage signal stored in the cine memory 150 and outputs the read imagesignal to the DSC 154. As a result, in the freeze mode, an ultrasoundimage (still image) based on the image signal read from the cine memory150 is displayed on the monitor 20.

The polarization processing unit 155 performs polarization processing,and is formed by a polarization circuit 156 and a circuit switch 158 asshown in FIG. 4 . The polarization circuit 156 forms a polarizationvoltage supply unit, and supplies a polarization voltage to theultrasound transducer 48. The polarization voltage is a voltage forpolarizing the ultrasound transducer 48 (strictly speaking, apiezoelectric element provided in the ultrasound transducer 48). Byapplying the polarization voltage to the electrodes of the ultrasoundtransducer 48, the ultrasound transducer 48 is polarized (that is, thealignment direction of the polarizer is one direction).

The polarization circuit 156 is electrically connected to all of theplurality of ultrasound transducers 48 through the universal cord 26 andthe coaxial cable 56. In the present embodiment, the polarizationcircuit 156 is provided separately from the transmission circuit 144 asshown in FIG. 4 , and supplies the polarization voltage to theultrasound transducer 48 in a period during which the operation mode isthe second mode. In addition, the polarization voltage is supplied fromthe polarization circuit 156 to the ultrasound transducer 48 through themultiplexer 140. In the present embodiment, the polarization voltage issupplied to m polarization target transducers simultaneously selected bythe multiplexer 140.

The polarization voltage may be a DC voltage or an AC voltage. In a casewhere the polarization voltage is an AC voltage, the waveform may be acontinuous waveform or a pulse waveform. In a case where the waveform ofthe polarization voltage is a pulse waveform, the waveform may be aunipolar pulse or a bipolar pulse.

As shown in FIG. 4 , the circuit switch 158 is connected to both thetransmission circuit 144 and the polarization circuit 156 at a positionbefore the multiplexer 140, and is a switch for switching to a circuitto be connected to the multiplexer 140 between the transmission circuit144 and the polarization circuit 156. The circuit switch 158 normallyconnects the transmission circuit 144 to the multiplexer 140. In thisstate, a driving voltage for ultrasound wave transmission is supplied tothe driving target transducer. On the other hand, at the time ofexecution of polarization processing, the circuit switch 158 switches acircuit to be connected to the multiplexer 140 from the transmissioncircuit 144 to the polarization circuit 156. In this state, apolarization voltage is supplied to the ultrasound transducer 48 to bepolarized.

The CPU 152 functions as a controller that controls each unit of theultrasound processor apparatus 14. As shown in FIG. 4 , the CPU 152 isconnected to the reception circuit 142, the transmission circuit 144,the A/D converter 146, the ASIC 148, the polarization circuit 156, andthe circuit switch 158 to control these devices. Specifically, the CPU152 is connected to the console 100 as shown in FIG. 4 , and controlseach unit of the ultrasound processor apparatus 14 according toexamination information and control parameters input through the console100 at the time of ultrasound diagnosis. As a result, an ultrasoundimage corresponding to the ultrasound image generation mode designatedby the operator is acquired. In particular, in the live mode, anultrasound image is acquired as needed at a fixed frame rate.

The CPU 152 automatically recognizes the ultrasound endoscope 12 basedon a method, such as Plug and Play (PnP), in a case where the ultrasoundendoscope 12 is connected to the ultrasound processor apparatus 14through the ultrasound connector 32 a. Thereafter, the CPU 152 accessesthe endoscope side memory 58 of the ultrasound endoscope 12 to read thecumulative value of the driving time stored in the endoscope side memory58. In addition, the CPU 152 accesses the endoscope side memory 58 atthe end of the ultrasound diagnosis, and updates the cumulative value ofthe driving time stored in the endoscope side memory 58 to a valueobtained by adding the time required for the ultrasound diagnosisperformed immediately before to the cumulative value of the driving timestored in the endoscope side memory 58.

In the present embodiment, the driving time is stored on the ultrasoundendoscope 12 side. However, the invention is not limited thereto, andthe driving time may be stored on the ultrasound processor apparatus 14side for each ultrasound endoscope 12.

In addition, in a case where predetermined conditions are satisfied in aperiod during which the operation mode is the second mode, the CPU 152controls the polarization processing unit 155 (specifically, thepolarization circuit 156 and the circuit switch 158) so that thepolarization processing unit 155 performs polarization processing. Inthe polarization processing, the polarization circuit 156 supplies apolarization voltage to the ultrasound transducer 48 to be polarized.The magnitude (potential) and the supply time of the polarizationvoltage supplied to the ultrasound transducer 48 in the polarizationprocessing are set to appropriate values by the CPU 152 according to thespecification of the ultrasound transducer 48 (specifically, thethickness, material, and the like of the piezoelectric element).Thereafter, the CPU 152 controls the polarization processing unit 155based on the set values described above. The magnitude and the supplytime of the polarization voltage are not limited to being automaticallyset by the CPU 152, and may be set to any values input through theconsole 100 by the operator.

Operation Example of Ultrasound Diagnostic Apparatus

Next, as an operation example of the ultrasound diagnostic apparatus 10,a flow of a series of processes relevant to ultrasound diagnosis(hereinafter, also referred to as diagnostic process) will be describedwith reference to FIGS. 5 to 7 . FIG. 5 is a diagram showing the flow ofthe diagnostic process using the ultrasound diagnostic apparatus 10.FIG. 6 is a diagram showing the procedure of a diagnostic step in thediagnostic process. FIG. 7 is a diagram showing the procedure of a scopechecking step in the diagnostic process.

In a case where each unit of the ultrasound diagnostic apparatus 10 ispowered on in a state in which the ultrasound endoscope 12 is connectedto the ultrasound processor apparatus 14, the endoscope processorapparatus 16, and the light source device 18, the diagnostic processstarts with the power-ON as a trigger. In a case where the diagnosticprocess starts, as shown in FIG. 5 , the operation mode is set to thesecond mode first (S001), and an input step is performed (S002). In theinput step, the operator inputs examination information, controlparameters, and the like through the console 100.

In a case where there is an instruction to start diagnosis after the endof the input step (Yes in S003), the operation mode is set to the firstmode (S004). Thereafter, the operator inserts the insertion part 22 ofthe ultrasound endoscope 12 into the body cavity of the patient, and theCPU 152 controls each unit of the ultrasound processor apparatus 14 inthe state to perform a diagnostic step (S005). The diagnostic stepproceeds along the flow shown in FIG. 6 . Specifically, in a case wherethe designated ultrasound image generation mode is a B mode (Yes inS011), the CPU 152 controls each unit of the ultrasound processorapparatus 14 to generate a B mode image (S012). In a case where thedesignated ultrasound image generation mode is a CF mode (Yes in S013),the CPU 152 controls each unit of the ultrasound processor apparatus 14to generate a CF mode image (S014). In a case where the designatedultrasound image generation mode is a PW mode (Yes in S015), the CPU 152controls each unit of the ultrasound processor apparatus 14 to generatea PW mode image (S016).

The generation of an ultrasound image in each mode is repeatedlyperformed until the diagnosis end conditions are satisfied (S017). Asthe diagnosis end conditions, for example, the operator gives aninstruction to end the diagnosis through the console 100.

In a case where the diagnosis end conditions are satisfied (Yes inS017), as shown in FIG. 6 , the CPU 152 accesses the endoscope sidememory 58 and updates the cumulative value of the driving time stored inthe endoscope side memory 58 by adding the time required for theultrasound diagnosis performed until then to the cumulative value of thedriving time stored in the endoscope side memory 58 (S018). Thediagnostic step ends at a point in time at which the series of steps(specifically, steps S011 to S018) in the diagnostic step end.Thereafter, the diagnostic process ends at a point in time at which eachunit of the ultrasound diagnostic apparatus 10 is powered off (Yes inS007).

Returning to the explanation of step S003 of the diagnostic process, ina case where there is no instruction to start diagnosis after the end ofthe input step (No in S003), a scope checking step is performed (S006).The scope checking step proceeds along the flow shown in FIG. 7 .Specifically, in the scope checking step, in a case where the checkingoperation unit 102 of the console 100 is operated by the operator (Yesin S021), the console 100 detects the operation (hereinafter, referredto as a checking operation) and transmits the detection result to theCPU 152 of the ultrasound processor apparatus 14.

In a case where the detection result of the checking operation isreceived, as shown in FIG. 7 , the CPU 152 controls the transmissioncircuit 144 to perform a state checking scan (S022). The state checkingscan is to control the transmission circuit 144 so that the drivingvoltage is supplied to each of the N ultrasound transducers 48 with allof the N ultrasound transducers 48 as driving target transducers. Morespecifically, in the state checking scan, a driving voltage is suppliedto the ultrasound transducer 48 as a driving target transducer at oneend of the N ultrasound transducers 48, and the driving targettransducer is shifted one by one and the supply of a driving voltage isrepeated up to the ultrasound transducer 48 at the other end. In thismanner, the N ultrasound transducers 48 are sequentially driven one byone to transmit and receive ultrasound waves.

In the present embodiment, the state checking scan is performed at atime at which the ultrasound endoscope 12 including the ultrasoundtransducer unit 46 is located outside the body cavity of the patient.That is, the state checking scan is performed in a state in which theultrasound transducer unit 46 is exposed in a room (hereinafter,referred to as a diagnostic room) where the ultrasound diagnosticapparatus 10 is disposed. More specifically, the state checking scan isperformed in a state in which the ultrasound transducer unit 46 faces asuitable place (for example, a place without people) in the diagnosticroom. In this case, each ultrasound transducer 48 that is a drivingtarget transducer receives the ultrasound wave reflected by the acousticmatching layer 76 as a reflected wave (echo) of the ultrasound wave.

Immediately after the execution of the state checking scan, as shown inFIG. 7 , the depolarization determination unit 170 calculates adepolarization determination value (S023). In step S023, thedepolarization determination unit 170 calculates, for each ultrasoundtransducer 48, reception sensitivity in a case where the ultrasoundtransducer unit 46 receives ultrasound waves (strictly speaking,ultrasound waves reflected by the acoustic matching layer 76) during thestate checking scan. Specifically, the depolarization determination unit170 is connected to the A/D converter 146 as shown in FIG. 4 . Thereception signal output from each ultrasound transducer 48 during thestate checking scan is digitally converted by the A/D converter 146, andis transmitted from each ultrasound transducer 48 to the depolarizationdetermination unit 170. The depolarization determination unit 170calculates the reception sensitivity for each ultrasound transducer 48based on the digitally converted reception signal (reception data). Thereception sensitivity for each ultrasound transducer 48 calculated asdescribed above corresponds to reception sensitivity at a time at whichthe ultrasound transducer unit 46 receives ultrasound waves with all ofthe N ultrasound transducers 48 as driving target transducers.

Here, the reception sensitivity of each ultrasound transducer 48reflects the degree of progress of depolarization of the ultrasoundtransducer 48. Specifically, the depolarization proceeds as the drivingtime of the ultrasound transducer 48 increases, and the receptionsensitivity decreases as the depolarization progresses. In addition, thereception sensitivity of each ultrasound transducer 48 varies as shownin FIG. 8A as the number of executions of ultrasound diagnosisincreases. This reflects that the number of driving target transducersand the driving frequency of each ultrasound transducer 48 changeaccording to the type (mode) of an ultrasound image formed in ultrasounddiagnosis. FIG. 8A is a diagram showing the reception sensitivity ofeach ultrasound transducer 48. #1, #2, ..., and #N in the diagramindicate numbers assigned for convenience to identify each ultrasoundtransducer 48, and a white circle plot directly above the ultrasoundtransducer 48 of each number indicates the reception sensitivity of theultrasound transducer 48.

Then, the depolarization determination unit 170 calculates adepolarization determination value from the reception sensitivitycalculated for each ultrasound transducer 48. The depolarizationdetermination unit 170 calculates one of the following (d1) to (d7) asthe depolarization determination value.

-   (d1) Variance of reception sensitivity of each ultrasound transducer    48 (hereinafter, referred to as a variance)-   (d2) Average value of reception sensitivity of each ultrasound    transducer 48 (hereinafter, referred to as an average value)-   (d3) Variance and average value-   (d4) Minimum value of reception sensitivity of each ultrasound    transducer 48 (hereinafter, referred to as a minimum value)-   (d5) Variance and minimum value-   (d6) Average value and minimum value-   (d7) Variance, average value, and minimum value

The variance is a statistical dispersion, is calculated with the Nultrasound transducers 48 as a population, and is calculated from thereception sensitivity of each of the N ultrasound transducers 48. Theaverage value is an arithmetic average value calculated from thereception sensitivity of each of the N ultrasound transducers 48. Theminimum value of the reception sensitivity of each ultrasound transducer48 is a minimum value (value closest to 0) among the receptionsensitivities of the N ultrasound transducers 48. Hereinafter, a casewhere the depolarization determination unit 170 calculates thedepolarization determination value (that is, the variance and theaverage value) shown in the above (d3) will be described as an example.However, it is needless to say that the following content can also beapplied to a case of calculating other depolarization determinationvalues (specifically, depolarization determination values shown in (d1),(d2), and any one of (d4) to (d7)).

After calculating the depolarization determination value, as shown inFIG. 7 , the depolarization determination unit 170 determines whether ornot the depolarization determination value satisfies the numericalconditions (S024). The numerical conditions are set for thedepolarization determination value, and are recorded on the ultrasoundprocessor apparatus 14 side. In a case where a plurality of types ofvalues are calculated as depolarization determination values, theabove-described numerical conditions are set for each depolarizationdetermination value. For example, in a case where a variance iscalculated as a depolarization determination value, an upper limit isset as the numerical conditions, and the depolarization determinationunit 170 determines whether or not the variance exceeds the upper limit.In a case where at least one of an average value or a minimum value iscalculated as a depolarization determination value, a lower limit is setas the numerical conditions, and the depolarization determination unit170 determines whether or not the calculated value (that is, at leastone of the average value or the minimum value) is less than the lowerlimit. The numerical conditions may be different for each ultrasoundendoscope 12, or may be common among the ultrasound endoscopes 12. Inaddition, the operator may be able to newly set or change the numericalconditions through the console 100.

Then, in a case where it is determined that the depolarizationdetermination value satisfies the numerical conditions (Yes in S024),the depolarization determination unit 170 transmits the determinationresult to the CPU 152. In a case where a plurality of types of values(for example, a variance and an average value) are calculated asdepolarization determination values, it is determined that any onedetermination value satisfies the numerical conditions, thedepolarization determination unit 170 transmits the determination resultto the CPU 152.

The above-described series of steps, that is, the checking scanexecution step S022, the depolarization determination value calculationstep S023, and the conditions determination step S024 regarding thedepolarization determination value are performed with a checkingoperation, which is performed by the operator through the checkingoperation unit 102 in a period during which the operation mode is thesecond mode, as a trigger. Then, the degree of progress ofdepolarization is estimated by the execution of steps S022, S023, andS024, and the depolarization progresses in a case where thedepolarization determination value satisfies the above-describednumerical conditions. Here, the degree of progress of the depolarizationis usually evaluated based on the reception sensitivity of theultrasound transducer 48, but the reception sensitivity of eachultrasound transducer 48 in the ultrasound transducer unit 46 variesbetween the ultrasound transducers 48. In a case where the ultrasoundtransducer unit 46 is a convex type probe, the variation is noticeable.For this reason, since it is not sufficient to determine the degree ofprogress of depolarization based only on the reception sensitivity ofone of the ultrasound transducers 48, it is necessary to determine thedegree of progress of the depolarization based on the above-describedvariation. Therefore, in the present embodiment, as described above, thereception sensitivity of each of the N ultrasound transducers 48 iscalculated, and the degree of progress of depolarization is determinedbased on the depolarization determination value calculated from thereception sensitivity of each ultrasound transducer 48.

Returning to the explanation of the scope checking step, as shown inFIG. 7 , in a case where the determination result indicating that thedepolarization determination value satisfies the numerical conditions isreceived, the CPU 152 controls the polarization processing unit 155(that is, the polarization circuit 156 and the circuit switch 158) sothat the polarization processing unit 155 performs polarizationprocessing (S025). That is, in a case where the depolarizationdetermination unit 170 determines that the depolarization determinationvalue satisfies the numerical conditions, the polarization circuit 156that is a polarization voltage supply unit supplies a polarizationvoltage to the ultrasound transducer 48 to be polarized through themultiplexer 140. In the present embodiment, the polarization processingis performed on all of the N ultrasound transducers 48. Specifically,half (that is, m ultrasound transducers 48) of the N ultrasoundtransducers 48 are polarized in the first half of the polarizationprocessing, and the other half of the ultrasound transducers 48 arepolarized in the second half.

By performing the polarization processing, as shown in FIG. 8B, eachultrasound transducer 48 is polarized (repolarized). Accordingly, thereception sensitivity of each ultrasound transducer 48 is restored, andthe reception sensitivities of the ultrasound transducers 48 becomeapproximately the same. FIG. 8B is a diagram showing the receptionsensitivity of each ultrasound transducer 48 immediately after thepolarization processing is performed, and is a diagram corresponding toFIG. 8A.

In a case where a variance and an average value are calculated asdepolarization determination value, the polarization processing isperformed in a case where at least one of the values satisfies thenumerical conditions. Therefore, for example, in a case where thereception sensitivities of the N ultrasound transducers 48 are entirelyreduced, it is possible to recover the reception sensitivity of eachultrasound transducer 48 by performing polarization processing in a casewhere the average value is lower than the lower limit even in a casewhere the variance does not exceed the upper limit.

After the polarization circuit 156 supplies a polarization voltage toeach of the N ultrasound transducers 48 in the polarization processing,as shown in FIG. 7 , the CPU 152 accesses the endoscope side memory 58to clear the cumulative value of the driving time stored in theendoscope side memory 58 (S026). As a result, the cumulative value ofthe driving time stored in the endoscope side memory 58 is set to theinitial value (that is, zero (0)). Then, the scope checking step ends ata point in time at which the cumulative value of the driving time iscleared. Also in a case where the depolarization determination unit 170determines that the depolarization determination value does not satisfythe numerical conditions in step S024 (No in S024), the scope checkingstep ends.

On the other hand, in a case where the checking operation is notperformed in step S021 (No in S021), the CPU 152 reads the cumulativevalue of the driving time from the endoscope side memory 58 anddetermines whether or not the cumulative value is equal to or greaterthan the threshold value (S027). The threshold value is set based on aninput operation performed by the operator through the threshold valueinput unit 104 of the console 100, and is stored, for example, on theultrasound processor apparatus 14 side. The threshold value may bedifferent for each ultrasound endoscope 12, or may be a value common tothe ultrasound endoscopes 12.

Then, in a case where it is determined that the above-describedcumulative value is equal to or greater than the threshold value, theCPU 152 controls the polarization processing unit 155 so that thepolarization processing unit 155 performs polarization processing asshown in FIG. 7 (S025). That is, in a case where the cumulative value ofthe driving time stored in the endoscope side memory 58 is equal to orgreater than the threshold value, the polarization circuit 156 suppliesa polarization voltage to the ultrasound transducer 48 to be polarizedthrough the multiplexer 140. Also in this case, the polarizationprocessing is performed on all of the N ultrasound transducers 48, and multrasound transducers 48 are polarized in each of the first half andthe second half of the polarization processing.

After the polarization processing is performed, as shown in FIG. 7 , theCPU 152 clears the cumulative value of the driving time stored in theendoscope side memory 58 (S026), and ends the scope checking step at apoint in time at which step S026 is completed. Also in a case where theCPU 152 determines that the cumulative value of the driving time is lessthan the threshold value in step S027 (No in S027), the scope checkingstep ends.

Effectiveness of Ultrasound Diagnostic Apparatus of the Invention

The characteristic of the ultrasound diagnostic apparatus of theinvention is that a depolarization determination value as an index valueregarding the state of the ultrasound transducer unit 46 is calculatedwith the operator’s operation on the checking operation unit 102 as atrigger, the necessity of polarization processing is determined from thedepolarization determination value, and the polarization processing isperformed in a case where it is determined that the polarizationprocessing is required. That is, in the ultrasound diagnostic apparatusof the invention, since the necessity of polarization processing isdetermined at a time at which the operator (user) operates the checkingoperation unit 102, it is possible to determine the necessity ofpolarization processing at the timing desired by the operator. That is,in the ultrasound diagnostic apparatus of the invention, since theexecution timing of the polarization processing is not limited to apredetermined timing unlike in the ultrasound diagnostic apparatusdescribed in JP2013-005137A, the degree of freedom in the executiontiming of the polarization processing is increased.

In addition, in the case of determining the necessity of polarizationprocessing based only on the cumulative value of the driving time of theultrasound transducer 48, even though the operator notices a decrease inthe reception sensitivity, it is determined that the polarizationprocessing is not yet required in a case where the cumulative value ofthe driving time at that point in time is less than the threshold value.In contrast, in the invention, in a case where the operator operates thechecking operation unit 102 at a time at which the operator notices adecrease in the reception sensitivity, the necessity of the polarizationprocessing is determined at that point in time. As a result, it ispossible to accurately perform the polarization processing at the timeat which the polarization processing is to be performed (for example, ina case where the cumulative value of driving time is less than thethreshold value but the reception sensitivity is noticeably reduced).

In addition, the ultrasound diagnostic apparatus of the invention doesnot require the reference transducer that is provided in the ultrasoundtransducer unit 46 in order to determine the necessity of polarizationprocessing (strictly speaking, the degree of progress of depolarization)in the ultrasound diagnostic apparatus described in JP2013-161955A.Therefore, in the ultrasound diagnostic apparatus of the invention, theultrasound transducer unit 46 is made smaller than that in the apparatusdescribed in JP2013-161955A. As a result, the operability (ease ofinsertion of the ultrasound endoscope 12 into the body cavity of thepatient) is improved.

In the ultrasound diagnostic apparatus of the invention, in the case ofdetermining the necessity of the polarization processing, the receptionsensitivities of all of the plurality of ultrasound transducers 48 arecalculated separately for each ultrasound transducer 48, thedepolarization determination value is calculated from the receptionsensitivity of each ultrasound transducer 48, and it is determinedwhether or not the depolarization determination value satisfies thenumerical conditions. That is, in the ultrasound diagnostic apparatus ofthe invention, the depolarization determination value can be calculatedfrom the reception sensitivities of all of the plurality of ultrasoundtransducers 48 based on the fact that the reception sensitivity (inother words, the degree of progress of depolarization) varies betweenthe ultrasound transducers 48, and the necessity of the polarizationprocessing can be determined based on the depolarization determinationvalue. As a result, a more appropriate determination result can beobtained as compared with the ultrasound diagnostic apparatus describedin JP2012-139460A in which a variation in the degree of progress ofdepolarization is not considered in the determination regarding thenecessity of the polarization processing.

Second Embodiment

In the embodiment described above, it is assumed that the checkingoperation unit 102 for checking the state of the ultrasound transducerunit 46 is provided in an apparatus other than the ultrasound endoscope12, specifically, in the console 100. However, the invention is notlimited thereto, and an embodiment in which the checking operation unitis provided in the ultrasound endoscope 12 (hereinafter, also referredto as a second embodiment) can also be considered.

Hereinafter, an ultrasound diagnostic apparatus according to the secondembodiment will be described with reference to FIG. 9 . FIG. 9 is ablock diagram showing the configurations of an ultrasound endoscope 12 xand an ultrasound processor apparatus 14 that are provided in theultrasound diagnostic apparatus according to the second embodiment.Hereinafter, the second embodiment will be described focusing on thedifferences from the above-described embodiment. In the secondembodiment, in FIG. 9 , elements in common with the above-describedembodiment are denoted by the same reference numerals as in theabove-described embodiment, and the description thereof will be omitted.

In the second embodiment, the checking operation unit 102 is notprovided in the console 100, while a checking operation unit 49 isprovided in the ultrasound endoscope 12. That is, in the secondembodiment, in the case of checking the state of the ultrasoundtransducer unit 46 (in other words, in the case of determining thenecessity of polarization processing), the operator operates thechecking operation unit 49 of the ultrasound endoscope 12. The checkingoperation unit 49 of the ultrasound endoscope 12 may be formed by, forexample, a push button, a slide switch, a dial switch, or a handle suchas a lever provided in the operation unit 24.

The checking operation unit 49 is connected to the CPU 152, and outputsa signal to the CPU 152 in a case where the checking operation unit 49is operated while the operation mode is the second mode. In a case wherethe output signal from the checking operation unit 49 is received, theCPU 152 performs a state checking scan. The subsequent procedures aresimilar to those in the above-described embodiment. As described above,in the second embodiment, since the checking operation unit 49 isprovided in the ultrasound endoscope 12, the operator can perform anoperation for checking the state of the ultrasound transducer unit 46while operating the ultrasound endoscope 12. As a result, it is possibleto improve the convenience of the operator. The second embodiment is thesame as the above-described embodiment except that the checkingoperation unit 49 is provided in the ultrasound endoscope 12.Accordingly, the same effect as in the above-described embodiment isobtained.

Third Embodiment

In the above-described embodiment, it is assumed that the state checkingscan is performed in a state in which the ultrasound transducer unit 46is exposed in the diagnostic room, specifically, the state checking scanis performed in a state in which the ultrasound transducer unit 46 facesa suitable place in the diagnostic room. In addition, in theabove-described embodiment, in the state checking scan, it is assumedthat each ultrasound transducer 48 that is a driving target transducerreceives the ultrasound wave reflected by the acoustic matching layer 76as a reflected wave (echo) of the ultrasound wave. However, theinvention is not limited thereto, and other methods can be considered asmethods for performing the state checking scan.

Hereinafter, an embodiment (hereinafter, referred to as a thirdembodiment) for performing a state checking scan using a methoddifferent from the methods of the above-described embodiments will bedescribed with reference to FIG. 10 . FIG. 10 is an explanatory diagramof the state checking scan in the third embodiment. Hereinafter, thethird embodiment will be described focusing on the differences from theabove-described embodiments. In the third embodiment, in FIG. 10 ,elements in common with the above-described embodiments are denoted bythe same reference numerals as in the above-described embodiments, andthe description thereof will be omitted.

In the third embodiment, the state checking scan is performed in a statein which the ultrasound endoscope 12 is not inserted into the bodycavity of the patient, that is, in a state in which the ultrasoundendoscope 12 is located outside the body of the patient. Morespecifically, in the third embodiment, a phantom F (for example, a humanmodel) shown in FIG. 10 is disposed outside the body of the patient. Atthe time of performing the state checking scan, the operator presses theultrasound transducer unit 46 (strictly speaking, the exposed surface ofthe acoustic lens 78) against the phantom F as shown in FIG. 10 .Thereafter, in a case where the operator operates the checking operationunit 102 in a state in which the ultrasound transducer unit 46 is incontact with the phantom F, the CPU 152 performs the state checking scanwith the operation as a trigger. In the state checking scan, theultrasound transducer unit 46 transmits and receives ultrasound wavesusing all of the N ultrasound transducers 48 as driving targettransducers. In this case, the ultrasound transducer unit 46 receives anultrasound wave (echo) reflected by the phantom F. Thereafter, thedepolarization determination unit 170 calculates the receptionsensitivity of each of the N ultrasound transducers 48 in the statechecking scan, and further calculates the depolarization determinationvalue. The subsequent procedures are similar to those in theabove-described embodiments.

As described above, in the third embodiment, the state checking scan isperformed using the phantom F, and the ultrasound transducer unit 46receives an ultrasound wave (echo) reflected by the phantom F in thestate checking scan. Since the strength of the ultrasound wave reflectedby the phantom F is usually larger than the strength of the ultrasoundwave reflected by the acoustic matching layer 76, it is possible tocalculate the reception sensitivity of each ultrasound transducer 48more appropriately by performing the state checking scan using thephantom F. The third embodiment is the same as the above-describedembodiments except that the state checking scan is performed using thephantom F. Accordingly, the same effect as in the above-describedembodiments is obtained.

Fourth Embodiment

In the above-described embodiments, the polarization voltage supply unitis formed by the polarization circuit 156 provided separately from thetransmission circuit 144, the invention is not limited thereto. Forexample, an embodiment in which the transmission circuit 144 is alsoused as a polarization voltage supply unit (hereinafter, also referredto as a fourth embodiment) can also be considered.

Hereinafter, an ultrasound diagnostic apparatus according to the fourthembodiment will be described with reference to FIGS. 11 and 12 . FIG. 11is a block diagram showing the configuration of an ultrasound processorapparatus 14 x according to the fourth embodiment. FIG. 12 is a diagramshowing the waveform of a polarization voltage supplied in the fourthembodiment. Hereinafter, the fourth embodiment will be describedfocusing on the differences from the above-described embodiments. In thefourth embodiment, in FIG. 11 , elements in common with theabove-described embodiments are denoted by the same reference numeralsas in the above-described embodiments, and the description thereof willbe omitted.

The ultrasound processor apparatus 14 x of the fourth embodiment doesnot comprise a device corresponding to the polarization processing unit155 as shown in FIG. 11 . On the other hand, in the fourth embodiment,the transmission circuit 144 forms a polarization voltage supply unit,and supplies a polarization voltage to each of the N ultrasoundtransducers 48 in a case where the polarization conditions are satisfiedin the scope checking step (that is, in a case where it is determinedthat polarization processing needs to be performed). That is, in thefourth embodiment, the CPU 152 controls the transmission circuit 144 sothat the transmission circuit 144 outputs a driving voltage in thediagnostic step and outputs a polarization voltage in the scope checkingstep.

In the fourth embodiment, the polarization voltage supplied by thetransmission circuit 144 is a pulse wave voltage similar to the drivingvoltage, more specifically, a unipolar pulse voltage. In the fourthembodiment, for the purpose of efficiently performing polarization, asshown in FIG. 12 , the CPU 152 controls the transmission circuit 144 sothat the polarization voltage, which is a unipolar pulse, isintermittently supplied a plurality of times from the transmissioncircuit 144. Here, a pulse wave interval (w in FIG. 12 ) corresponds toa plurality of clock signals input to the transmission circuit 144,specifically, an interval of a degree that a plurality of polarizationvoltage waveforms intermittently arranged form a DC waveform in a pseudomanner. For the purpose of bringing the waveform of the polarizationvoltage close to the DC waveform, the interval described above ispreferably as short as possible. In particular, it is preferable to setthe interval described above to an interval corresponding to the minimumclock.

As described above, in the fourth embodiment, since the transmissioncircuit 144 forms a polarization voltage supply unit, it is possible topolarize the ultrasound transducer 48 using the existing transmissioncircuit 144. As a result, since it is not necessary to separatelyprovide the polarization circuit 156, the hardware configuration of theultrasound processor apparatus 14 x is simplified accordingly. In thisrespect, the fourth embodiment is preferable. On the other hand,providing the transmission circuit 144 and the polarization circuit 156separately is advantageous in that it is possible to shorten the time ofpolarization processing. In this respect, the above-describedembodiments are preferable.

In addition, the fourth embodiment is different from the above-describedembodiments in that the transmission circuit 144 forms a polarizationvoltage supply unit but is the same as the above-described embodimentsother than that. Therefore, the same effect as in the above-describedembodiments is obtained.

EXPLANATION OF REFERENCES

-   10: ultrasound diagnostic apparatus-   12: ultrasound endoscope-   12 x: ultrasound endoscope-   14: ultrasound processor apparatus-   14 x: ultrasound processor apparatus-   16: endoscope processor apparatus-   18: light source device-   20: monitor-   21 a: water supply tank-   21 b: suction pump-   21 c: air supply pump-   22: insertion part-   24: operation unit-   26: universal cord-   28 a: air and water supply button-   28 b: suction button-   30: treatment tool insertion port-   32 a: ultrasound connector-   32 b: endoscope connector-   32 c: light source connector-   36: ultrasound observation portion-   37: balloon-   38: endoscope observation portion-   40: distal end portion-   42: bending portion-   43: flexible portion-   44: treatment tool lead-out port-   45: treatment tool channel-   46: ultrasound transducer unit-   47: water supply port-   48: ultrasound transducer-   49: checking operation unit-   50: ultrasound transducer array-   54: backing material layer-   56: coaxial cable-   58: endoscope side memory-   60: FPC-   76: acoustic matching layer-   78: acoustic lens-   82: observation window-   84: objective lens-   86: solid-state imaging element-   88: illumination window-   90: cleaning nozzle-   92: wiring cable-   100: console-   102: checking operation unit-   104: threshold value input unit-   140: multiplexer-   142: reception circuit-   144: transmission circuit-   146: A/D converter-   148: ASIC-   150: cine memory-   151: memory controller-   152: CPU-   154: DSC-   155: polarization processing unit-   156: polarization circuit-   158: circuit switch-   160: phase matching unit-   162: B mode image generation unit-   164: PW mode image generation unit-   166: CF mode image generation unit-   170: depolarization determination unit-   F: phantom

What is claimed is:
 1. An ultrasound system, comprising: an ultrasoundprobe including an array of ultrasound transducers; a transmissioncircuit having transmit channels coupled to the ultrasound transducers;and a controller with computer readable instructions stored onnon-transitory memory that when executed during operation of theultrasound system, cause the controller to: apply an imaging transmitsignal for processing in one or more modes via the transmission circuitto the ultrasound probe; and apply a repolarization transmit signal forprocessing in one or more modes via the transmission circuit to theultrasound probe one or more of before, after, or interleaved betweenexecution of the imaging transmit signal for processing in one or moremodes.
 2. The ultrasound system according to claim 1, wherein theimaging transmit signal is different and separate from therepolarization transmit signal, and wherein an amplitude of therepolarization transmit signal is greater than an amplitude of theimaging transmit signal.
 3. The ultrasound system according to claim 1,wherein the imaging transmit signal includes one of a b-mode pulsesignal and a harmonic pulse signal.
 4. The ultrasound system accordingto claim 1, wherein the ultrasound transducers are single crystaltransducers.
 5. An ultrasound image generation method, comprising:executing processing in one or more ultrasound image generation modeswith an ultrasound transducer; and causing the ultrasound transducer toexecute polarization processing mode for repolarization one or more ofbefore, after, and interleaved between execution in the one or moreultrasound image generation modes, wherein the polarization processingis different and separate from the one or more ultrasound imagegeneration modes.
 6. The ultrasound image generation method according toclaim 5, wherein the executing processing in one or more ultrasoundimage generation modes includes sending an imaging input signal adaptedfor ultrasound image generation to the ultrasound transducer.
 7. Theultrasound image generation method according to claim 5, wherein theultrasound transducer is a single crystal transducer.
 8. The ultrasoundimage generation method according to claim 6, wherein the causing theultrasound transducer to execute the polarization processing includessending one or more signals of a polarization voltage adapted forrepolarization of the ultrasound transducer to the ultrasoundtransducer, and wherein the polarization voltage is different andseparate from the imaging input signal adapted for imaging.
 9. Theultrasound image generation method according to claim 5, wherein thecausing the ultrasound transducer to execute the polarization processingis responsive to a user’s input received at least one of before, after,or interleaved between executing the one or more ultrasound imagegeneration modes.
 10. The ultrasound image generation method accordingto claim 5, wherein the causing the ultrasound transducer to execute thepolarization processing occurs automatically after and in response to aset threshold number of image generation pulses of the one or moreultrasound image generation modes being executed, and wherein thecausing the ultrasound transducer to execute the polarization processingincludes applying a number of repolarization pulses, and wherein thenumber of repolarization pulses is less than the threshold number ofimage generation pulses.
 11. The ultrasound image generation methodaccording to claim 5, further comprising: determining a sensitivitylevel of the ultrasound transducer during the executing the one or moreultrasound image generation modes, wherein the causing the ultrasoundtransducer to execute the polarization processing occurs automatically,in response to the determined sensitivity level decreasing to athreshold sensitivity level.
 12. The ultrasound image generation methodaccording to claim 11, wherein the causing the ultrasound transducer toexecute the polarization processing occurs after a conclusion of oneultrasound image generation mode of the one or more ultrasound imagegeneration modes that is occurring while the sensitivity level of theultrasound transducer is determined to be at or below the thresholdsensitivity level and before executing a subsequent ultrasound imagegeneration mode of the one or more ultrasound image generation modes.13. The ultrasound image generation method according to claim 11,wherein the determined sensitivity level is based on an amplitude ofechoes received by the ultrasound transducer during executing the one ormore ultrasound image generation modes.
 14. The ultrasound imagegeneration method according to claim 5, further comprising: determiningimage quality deterioration of an image generated from an echo signalreceived as a result of executing the one or more ultrasound imagegeneration modes, wherein the causing the ultrasound transducer toexecute the polarization processing occurs automatically in response tothe determined image quality deterioration.
 15. An ultrasound imagegeneration method, comprising: executing an ultrasound image generationmode by applying one or more imaging transmit pulses adapted for imagingto an ultrasound transducer; determining a sensitivity of the ultrasoundtransducer during executing the ultrasound image generation mode; and inresponse to the determined sensitivity decreasing to a threshold level,causing the ultrasound transducer to execute polarization processingfollowing a conclusion of the executed ultrasound image generation mode.16. The ultrasound image generation method according to claim 15,wherein the causing the ultrasound transducer to execute thepolarization processing includes applying one or more repolarizationtransmit pulses adapted for repolarization to the ultrasound transducer,and wherein the repolarization transmit pulses are different from andoccur separately from the one or more imaging transmit pulses.
 17. Theultrasound image generation method according to claim 15, wherein theone or more imaging transmit pulses include a first number of imagingtransmit pulses, and wherein the causing the ultrasound transducer toexecute the polarization processing includes applying a second number ofrepolarization transmit pulses to the ultrasound transducer, the secondnumber being less than the first number.
 18. The ultrasound imagegeneration method according to claim 17, wherein the second number isdetermined in response to the sensitivity of the ultrasound transducer.19. The ultrasound image generation method according to claim 15,wherein the executing the ultrasound image generation mode includessending an imaging input signal adapted for ultrasound image generationto the ultrasound transducer.
 20. The ultrasound image generation methodaccording to claim 19, wherein the ultrasound transducer is a singlecrystal transducer.